Method and apparatus for adjustment of sequential biventricular pacing parameters

ABSTRACT

A method and system are disclosed for setting the pacing parameters utilized by an implantable cardiac device in delivering cardiac resynchronization therapy. The system may, in different embodiments, be implemented in programming of the implantable device and an external programmer in communication therewith or in the programming of the implantable device by itself. The selection of the pacing parameters is based at least in part upon measurements of intrinsic cardiac conduction parameters. Among the pacing parameters which may be selected in this way are the atrio-ventricular delay interval used in atrial-tracking and AV sequential pacing modes and the biventricular offset interval.

RELATED APPLICATIONS

This application is a continuation-in-part of U.S. patent applicationSer. No. 10/352,780, filed on Jan. 28, 2003, now issued as U.S. Pat. No.7,013,176, the disclosure of which is incorporated by reference.

FIELD OF THE INVENTION

This invention pertains to cardiac rhythm management devices such aspacemakers and other implantable devices for treating cardiacdysfunction.

BACKGROUND

Cardiac rhythm management devices are implantable devices that provideelectrical stimulation to selected chambers of the heart in order totreat disorders of cardiac rhythm. A pacemaker, for example, is acardiac rhythm management device that paces the heart with timed pacingpulses. The most common condition for which pacemakers are used is inthe treatment of bradycardia, where the ventricular rate is too slow.Atrio-ventricular conduction defects (i.e., AV block) that are permanentor intermittent and sick sinus syndrome represent the most common causesof bradycardia for which permanent pacing may be indicated. Iffunctioning properly, the pacemaker makes up for the heart's inabilityto pace itself at an appropriate rhythm in order to meet metabolicdemand by enforcing a minimum heart rate and/or artificially restoringAV conduction.

Pacing therapy can also be used in the treatment of heart failure, whichrefers to a clinical syndrome in which an abnormality of cardiacfunction causes a below normal cardiac output that can fall below alevel adequate to meet the metabolic demand of peripheral tissues. Whenuncompensated, it usually presents as congestive heart failure due tothe accompanying venous and pulmonary congestion. Heart failure can bedue to a variety of etiologies with ischemic heart disease being themost common. It has been shown that some heart failure patients sufferfrom intraventricular and/or interventricular conduction defects (e.g.,bundle branch blocks) such that their cardiac outputs can be increasedby improving the synchronization of ventricular contractions withelectrical stimulation. In order to treat these problems, implantablecardiac devices have been developed that provide appropriately timedelectrical stimulation to one or more heart chambers in an attempt toimprove the coordination of atrial and/or ventricular contractions,termed cardiac resynchronization therapy (CRT). Ventricularresynchronization is useful in treating heart failure because, althoughnot directly inotropic, resynchronization can result in a morecoordinated contraction of the ventricles with improved pumpingefficiency and increased cardiac output. Currently, a most common formof CRT applies stimulation pulses to both ventricles, eithersimultaneously or separated by a specified biventricular offsetinterval, and after a specified atrio-ventricular delay interval withrespect to the detection of an intrinsic atrial contraction. Appropriatespecification of these pacing parameters is necessary in order toachieve optimum improvement in cardiac function, and it is this problemwith which the present invention is primarily concerned.

SUMMARY

The present invention relates to a system and method for optimallydetermining pacing parameters for delivering cardiac resynchronizationtherapy. The system may include an implantable cardiac rhythm managementdevice and an external programmer in communication therewith or theimplantable device alone. In accordance with the invention, the systemmeasures one or more intrinsic conduction parameters from electrogramsignals generated during intrinsic beats. Optimum pre-excitation timingparameters may then be determined in accordance with formulas thatrelate the optimum pre-excitation timing parameter to the measuredintrinsic conduction parameters as defined by a set of specifiedcoefficients. The specified coefficients may be pre-derived from alinear regression analysis of clinical population data relatingparticular values of the measured intrinsic conduction parameters to anoptimum value of the pre-excitation timing parameter as determined byconcurrent measurement of another parameter reflective of cardiacfunction. Pre-excitation timing parameters which may be optimallydetermined in this manner are the biventricular offset interval whichseparates right and left ventricular paces and the atrio-ventriculardelay interval used in atrial-tracking or AV sequential pacing.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a block diagram of an exemplary cardiac device for practicingthe present invention.

FIG. 2 illustrates an exemplary algorithm for calculating theatrio-ventricular delay interval used in atrial-tracking and AVsequential pacing modes.

FIG. 3 illustrates an exemplary algorithm for measuring intrinsicconduction parameters.

FIG. 4 illustrates an exemplary algorithm for determining the locationof a left ventricular lead.

FIG. 5 illustrates an exemplary algorithm for measuring the relativeintrinsic AV conduction delays at two left ventricular sites.

FIG. 6 illustrates an exemplary algorithm for selecting between twoalternative left ventricular pacing sites.

FIG. 7 illustrates an exemplary algorithm for determining an optimalbiventricular offset interval.

FIG. 8 illustrates an exemplary algorithm for determining separateatrio-ventricular delays for each ventricle.

DETAILED DESCRIPTION

Applying cardiac resynchronization therapy in the most efficaciousmanner requires optimal selection of a number of pacing parameters.Described below is a cardiac rhythm management device configurable fordelivering resynchronization pacing to the left ventricle (LV) and/orthe right ventricle (RV) in order to compensate for ventricularconduction delays and improve the coordination of ventricularcontractions. In accordance with the present invention, a number ofthese parameters may be set or adjusted based upon measurements ofintra-cardiac conduction times using the sensing channels of animplanted device. Algorithms for setting these pacing parameters may beimplemented in either the programming of an external programmer or inthe programming of the implanted device itself or as a printed lookuptable procedure. In the former embodiment, the external programmercommunicates with the implantable device over a telemetry link andreceives either raw electrogram data, markers corresponding toparticular sensed events, or measurements of the intervals betweenparticular sensed events as computed by the implantable device. Theexternal programmer may then compute optimal settings for pacingparameters which are either transmitted to the implantable device forimmediate reprogramming or presented to a clinician operating theexternal programmer as recommendations. In another embodiment, theimplantable device is programmed to automatically set certain pacingparameters in accordance with information gathered from its sensingchannels. Among the pacing parameters which may be set by either ofthese embodiments are the selection of which heart chambers are to bepaced, the atrio-ventricular delay interval, the biventricular offsetinterval, and selection between alternative LV pacing sites.

1. Exemplary Device Description

Conventional cardiac pacing with implanted pacemakers involvesexcitatory electrical stimulation of the heart by the delivery of pacingpulses to an electrode in electrical contact with the myocardium. Thepacemaker is usually implanted subcutaneously on the patient's chest,and is connected to electrodes by leads threaded through the vessels ofthe upper venous system into the heart. An electrode can be incorporatedinto a sensing channel that generates an electrogram signal representingcardiac electrical activity at the electrode site and/or incorporatedinto a pacing channel for delivering pacing pulses to the site.

A block diagram of an implantable multi-site pacemaker having multiplesensing and pacing channels is shown in FIG. 1. (As the term is usedherein, a “pacemaker” should be taken to mean any cardiac rhythmmanagement device, such as an implantable cardioverter/defibrillator,with a pacing functionality.) The controller of the pacemaker is made upof a microprocessor 10 communicating with a memory 12 via abidirectional data bus, where the memory 12 typically comprises a ROM(read-only memory) for program storage and a RAM (random-access memory)for data storage. The controller could be implemented by other types oflogic circuitry (e.g., discrete components or programmable logic arrays)using a state machine type of design, but a microprocessor-based systemis preferable. As used herein, the programming of a controller should betaken to refer to either discrete logic circuitry configured to performparticular functions or to the code executed by a microprocessor. Thecontroller is capable of operating the pacemaker in a number ofprogrammed modes where a programmed mode defines how pacing pulses areoutput in response to sensed events and expiration of time intervals. Atelemetry interface 80 is provided for communicating with an externalprogrammer 300. The external programmer is a computerized device with anassociated display and input means that can interrogate the pacemakerand receive stored data as well as directly adjust the operatingparameters of the pacemaker. As described below, in certain embodimentsof a system for setting pacing parameters, the external programmer maybe utilized for computing optimal pacing parameters from data receivedfrom the implantable device over the telemetry link which can then beset automatically or presented to a clinician in the form ofrecommendations.

The embodiment shown in FIG. 1 has three sensing/pacing channels, wherea pacing channel is made up of a pulse generator connected to anelectrode while a sensing channel is made up of the sense amplifierconnected to an electrode. A MOS switching network 70 controlled by themicroprocessor is used to switch the electrodes from the input of asense amplifier to the output of a pulse generator. The switchingnetwork 70 also allows the sensing and pacing channels to be configuredby the controller with different combinations of the availableelectrodes. The channels may be configured as either atrial orventricular channels allowing the device to deliver conventionalventricular single-site pacing with or without atrial tracking,biventricular pacing, or multi-site pacing of a single chamber. In anexample configuration, a right atrial sensing/pacing channel includesring electrode 43 a and tip electrode 43 b of bipolar lead 43 c, senseamplifier 41, pulse generator 42, and a channel interface 40. A rightventricular sensing/pacing channel includes ring electrode 23 a and tipelectrode 23 b of bipolar lead 23 c, sense amplifier 21, pulse generator22, and a channel interface 20, and a left ventricular sensing/pacingchannel includes ring electrode 33 a and tip electrode 33 b of bipolarlead 33 c, sense amplifier 31, pulse generator 32, and a channelinterface 30. The channel interfaces communicate bi-directionally with aport of microprocessor 10 and include analog-to-digital converters fordigitizing sensing signal inputs from the sensing amplifiers, registersthat can be written to for adjusting the gain and threshold values ofthe sensing amplifiers, and registers for controlling the output ofpacing pulses and/or changing the pacing pulse amplitude. In thisembodiment, the device is equipped with bipolar leads that include twoelectrodes which are used for outputting a pacing pulse and/or sensingintrinsic activity. Other embodiments may employ unipolar leads withsingle electrodes for sensing and pacing. The switching network 70 mayconfigure a channel for unipolar sensing or pacing by referencing anelectrode of a unipolar or bipolar lead with the device housing or can60.

The controller 10 controls the overall operation of the device inaccordance with programmed instructions stored in memory. The controller10 interprets electrogram signals from the sensing channels and controlsthe delivery of paces in accordance with a pacing mode. The sensingcircuitry of the pacemaker generates atrial and ventricular electrogramsignals from the voltages sensed by the electrodes of a particularchannel. An electrogram is analogous to a surface EKG and indicates thetime course and amplitude of cardiac depolarization and repolarizationthat occurs during either an intrinsic or paced beat. When anelectrogram signal in an atrial or ventricular sensing channel exceeds aspecified threshold, the controller detects an atrial or ventricularsense, respectively, which pacing algorithms may employ to trigger orinhibit pacing.

2. Cardiac Resynchronization Pacing Therapy

Cardiac resynchronization therapy is most conveniently delivered inconjunction with a bradycardia pacing mode. Bradycardia pacing modesrefer to pacing algorithms used to pace the atria and/or ventricles in amanner that enforces a certain minimum heart rate. Because of the riskof inducing an arrhythmia with asynchronous pacing, most pacemakers fortreating bradycardia are programmed to operate synchronously in aso-called demand mode where sensed cardiac events occurring within adefined interval either trigger or inhibit a pacing pulse. Inhibiteddemand pacing modes utilize escape intervals to control pacing inaccordance with sensed intrinsic activity. In an inhibited demand mode,a pacing pulse is delivered to a heart chamber during a cardiac cycleonly after expiration of a defined escape interval during which nointrinsic beat by the chamber is detected. For example, a ventricularescape interval for pacing the ventricles can be defined betweenventricular events, referred to as the cardiac cycle (CC) interval withits inverse being the lower rate limit or LRL. The CC interval isrestarted with each ventricular sense or pace. In atrial tracking and AVsequential pacing modes, another ventricular escape interval is definedbetween atrial and ventricular events, referred to as theatrio-ventricular pacing delay interval or AVD, where a ventricularpacing pulse is delivered upon expiration of the atrio-ventricularpacing delay interval if no ventricular sense occurs before. In anatrial tracking mode, the atrio-ventricular pacing delay interval istriggered by an atrial sense and stopped by a ventricular sense or pace.An atrial escape interval can also be defined for pacing the atriaeither alone or in addition to pacing the ventricles. In an AVsequential pacing mode, the atrio-ventricular delay interval istriggered by an atrial pace and stopped by a ventricular sense or pace.Atrial tracking and AV sequential pacing are commonly combined so thatthe AVD starts with either an atrial pace or sense.

As described above, cardiac resynchronization therapy is pacingstimulation applied to one or more heart chambers in a manner thatcompensates for conduction delays. Ventricular resynchronization pacingis useful in treating heart failure in patients with interventricular orintraventricular conduction defects because, although not directlyinotropic, resynchronization results in a more coordinated contractionof the ventricles with improved pumping efficiency and increased cardiacoutput. Ventricular resynchronization can be achieved in certainpatients by pacing at a single unconventional site, such as the leftventricle instead of the right ventricle in patients with leftventricular conduction defects. Resynchronization pacing may alsoinvolve biventricular pacing with the paces to right and left ventriclesdelivered either simultaneously or sequentially, with the intervalbetween the paces termed the biventricular offset (BVO) interval (alsosometimes referred to as the LV offset (LVO) interval or VV delay). Theoffset interval may be zero in order to pace both ventriclessimultaneously, or non-zero in order to pace the left and rightventricles sequentially. For one embodiment, the offset interval issigned, with a positive value indicating a pace to the left after theright and a negative value indicating a pace to the left before theright. For another embodiment, the offset interval is the unsigneddifference between the atrioventricular pacing delay for the first pacedventricle and the atrioventricular pacing delay for the second pacedventricle.

Cardiac resynchronization therapy is most commonly applied in thetreatment of patients with heart failure due to left ventriculardysfunction which is either caused by or contributed to by leftventricular conduction abnormalities. In such patients, the leftventricle or parts of the left ventricle contract later than normalduring systole which thereby impairs pumping efficiency. In order toresynchronize ventricular contractions in such patients, pacing therapyis applied such that the left ventricle or a portion of the leftventricle is pre-excited relative to when it would become depolarized inan intrinsic contraction. Optimal pre-excitation in a given patient maybe obtained with biventricular pacing or with left ventricular-onlypacing.

3. Optimal Adjustment of Pre-Excitation Timing Parameters

Once a particular resynchronization pacing mode is selected for apatient, pacing parameters affecting the manner and extent to whichpre-excitation is applied must be specified. Such pre-excitation timingparameters would include, for example, the atrio-ventricular pacingdelay (AVD) and the biventricular offset interval. The biventricularoffset interval determines the manner in which the left ventricle ispre-excited relative to right ventricular events. The length of thespecified AVD relative to the intrinsic atrio-ventricular delay dictateshow early in the cardiac cycle that pacing stimulation is firstdelivered to the ventricles and, therefore, the amount of pre-excitationdelivered to the patient. In order to optimally specify theseparameters, the patient may be subjected to clinical hemodynamic testingafter implantation where the parameters are varied as cardiac functionis assessed. For example, a patient may be given resynchronizationstimulation while varying pre-excitation timing parameters in order todetermine the values of the parameters that result in maximum cardiacperformance, as determined by measuring a parameter reflective ofcardiac function such as maximum left ventricular pressure change(dP/dt).

Determining optimal pacing parameters for an individual patient byclinical hemodynamic testing, however, is difficult and costly. It wouldbe advantageous if such optimal pacing parameters could be determinedfrom measurements of intrinsic conduction parameters which reflect howexcitation is conducted within the patient's heart during intrinsicbeats. In the approach of the present invention, therefore, intrinsicconduction data is collected from a surface EKG or from the sensingchannels of the implantable cardiac resynchronization device and thenused to compute optimum values of resynchronization pacing parameters.The technique for setting pacing parameters may be implemented as asystem in which an external programmer presents intrinsic conductiondata to a clinician who then manually programs the implantable devicewith parameters computed from the intrinsic conduction data (by, forexample, using a printed lookup table and procedure). The technique mayalso be implemented as an automated system for setting optimal pacingparameters. The automated system may be made up of the implantabledevice alone or an external programmer in communication with theimplantable device via a wireless telemetry link. The system may eitherautomatically set the pacing parameters of the implantable device to thecomputed optimum values or present the optimum values to a clinician inthe form of a recommendation. In one embodiment, one or more intrinsicconduction parameters is measured from electrogram signals generated bythe sensing channels of an implantable cardiac resynchronization deviceduring intrinsic beats, where the measured intrinsic conductionparameters may represent averages of values obtained during a specifiednumber of intrinsic beats. The automated system, or a clinician manuallyprogramming the device, then computes a pre-excitation timing parametersuch as the AVD or biventricular offset interval in accordance with aformula that equates an optimum value of the pre-excitation timingparameter to a linear sum of the measured intrinsic conductionparameters multiplied by specified coefficients.

In order to pre-derive the specified coefficients for later programminginto the system or for use by a clinician, clinical population data isobtained that relates particular values of the measured intrinsicconduction parameters to an optimum value of the pre-excitation timingparameter as determined by concurrent measurement of another parameterreflective of cardiac function (e.g., maximum dP/dt or minimum atrialrate). A linear regression analysis is then performed to derive valuesof the specified coefficients used in the formula for setting thepre-excitation timing parameter, the specified coefficients thus beingregression coefficients.

a. Optimal Adjustment of AVD

The AVD interval determines the amount of pre-excitation delivered byresynchronization, and its optimum value in any particular patientdepends on the patient's intrinsic atrio-ventricular intervals and thedegree of the patient's conduction pathology. The latter is related tothe duration of ventricular depolarization during an intrinsiccontraction as reflected by the QRS width in a surfaceelectrocardiogram. It has been found empirically that patients can becategorized into two groups according to how well they respond toresynchronization therapy. It has also been found that patients can beidentified as being in one group or another based upon their measuredQRS widths. Strong responders, who exhibit a high degree of improvementin systolic function with resynchronization pacing, can be identified aspatients with a QRS width greater than 150 milliseconds. Weakresponders, who exhibit less improvement with resynchronization pacing,can be identified as patients with a QRS width less than or equal to 150milliseconds. Within each of the two groups, a linear relationship hasbeen found to exist between the optimal AVD interval forresynchronization pacing and the patient's measured intrinsicatrio-ventricular interval (AVI). Thus, in one embodiment, the optimumAVD interval may be determined by the following formulas:AVD=a ₁ AVI+a ₂ (for QRS>150 milliseconds)orAVD=b ₁ AVI+b ₂ (for QRS<150 milliseconds)where the coefficients a₁, a₂, b₁, and b₂ are obtained from a regressionanalysis of representative population data. The intrinsic AV intervaland QRS width can be determined either from a surface EKG or anintra-cardiac electrogram.

Categorizing patients into only two groups based upon QRS widthnecessarily has a limited sensitivity and specificity. It has furtherbeen found, however, that optimal AVD intervals for resynchronizationpacing can be based upon a formula which is a continuous function ofboth QRS width (or other parameter reflective of depolarizationduration) and the measured intrinsic AV delay interval. That is:AVD=k ₁ AVI+k ₃ QRS+k ₄

A further refinement of the above formula is to use separately measuredintrinsic AV delay intervals for the right and left ventricles as couldbe obtained from the right ventricular and left ventricular sensingchannels of an implanted cardiac device:AVD=k ₁ AV _(R) +k ₂ AV _(L) +k ₃ QRS+k ₄where AV_(R) is the intrinsic AV interval for the right ventricle andAV_(L) is the intrinsic AV interval for the left ventricle.

As noted above, intrinsic conduction parameters for computing theoptimum AV delay may be obtained from intra-cardiac electrogramsgenerated by the implanted device's sensing channels. The system maytherefore be programmed to measure intrinsic conduction parameters fromelectrogram signals and use them in a formula with coefficients obtainedby linear regression as described above to compute the optimum AVD. Thesystem may be programmed to automatically set the programmed AVDinterval in accordance with the computed optimum AVD interval or torecommend to an operator of the external programmer that the programmedAVD interval be set to the computed optimum AVD interval. The measuredintrinsic conduction parameters may constitute either singlemeasurements or averages of a plurality of measurements.

FIG. 2 illustrates an exemplary implementation of the above-describedmethod for determining the optimum AVD as could be executed by anappropriately programmed processor of the implantable cardiac device orexternal programmer. In this embodiment, the optimum AVD is obtainedaccording to the following formula:AVD=k ₁ AV _(R) +k ₂ AQ* _(L) +k ₃ Q*S*+k ₄where AV_(R) is the right intrinsic atrio-ventricular delay measured asthe interval between an atrial sense and a right ventricular sense,AQ*_(L) is the left intrinsic atrio-ventricular delay measured as theinterval between an atrial sense and the start of left ventriculardepolarization in an electrogram, and Q*S* is the duration ofventricular depolarization measured as the interval from the start ofleft ventricular depolarization to the end of left ventriculardepolarization in an electrogram. The start and end of depolarizationmay be detected by the implantable device from an electrogram using athreshold criterion similar to that used for detecting chamber senses.The specified coefficients are k₁, k₂, k₃, and k₄, where different setsof coefficients are used depending upon which chambers are paced in thecurrently programmed mode and the location of the left ventricularpacing lead. Each set of specified coefficients may be derived by aregression analysis of clinical data relating the optimum AVD to themeasured intrinsic conduction parameters using a pacing mode for pacinga particular chamber or chambers and using a particular location for theleft ventricular pacing lead.

Still referring to FIG. 2, the system determines at steps A1 and A2whether the implantable device is operating in a right ventricular-onlypacing mode (RV mode), biventricular pacing mode (BV mode), or leftventricular-only pacing mode (LV mode). If in RV mode, specifiedcoefficients for optimum setting of the AVD interval in that mode areobtained at step A5 e. If in BV mode, the system determines at step A3whether the left ventricular pacing lead is in an anterior or lateralventricular location, the latter corresponding to the left ventricularfree wall. If the left ventricular pacing lead is lateral, specifiedcoefficients for optimum setting of the AVD in that situation areobtained at step A5 a, while if the left ventricular pacing lead isanterior, specified coefficients for optimum setting of the AVD areobtained at step A5 b. Similarly, if it is determined at step A2 thatthe device is operating in LV mode, the left ventricular pacing leadlocation is determined at step A4 so that specified coefficients forsetting the AVD are obtained at either step A5 c or A5 d in accordancewith whether the left ventricular pacing lead location is lateral oranterior, respectively. The calculated AVD value is next compared withthe right intrinsic atrio-ventricular delay at step A7. If thecalculated AVD value is greater than the right intrinsicatrio-ventricular delay, the AVD is set to the value of the latter plusa specified margin (in this case, 30 ms). At steps A9 through A12, thecalculated AVD is compared with specified maximum and minimum limitvalues (300 and 50 ms, respectively, in this case). If the calculatedAVD exceeds the maximum limit value, the AVD is set to the maximum limitvalue. If the calculated AVD is below the minimum limit value, the AVDis set to the minimum limit value. In an alternative embodiment, if thecalculated AVD value is greater than the minimum of a fixed percentageof the right intrinsic atrio-ventricular delay (e.g., 70%) or a fixedvalue (e.g., 300 ms), the AVD is set to the shorter of the two values(i.e., either the fixed percentage of the intrinsic AV delay or thefixed value) or set to a minimum limit value if the calculated AVD isless than the minimum limit value.

Alternative formulas for calculating the AVD using different intrinsicconduction parameters may also be employed, examples of which are:AVD=k ₁ AV _(R) +k ₂ AV _(L) +k ₃ Q*S*+k ₄AVD=k ₁ AV _(R) +k ₂ Q*S*+k ₃AVD=k ₁ AV _(L) +k ₂ AV _(R) +k ₃AVD=k ₁ AV _(R) +k ₂ QRS+k ₃where AV_(L) is the left intrinsic atrio-ventricular delay measured asthe interval between an atrial sense and a left ventricular sense, andQRS is the width of the QRS complex as determined from a surfaceelectrocardiogram. Which formula would produce the best results in agiven situation would depend upon both the individual patient and theparticular implanted device. Tables 1 through 3 show example values ofspecified coefficients for calculating the AVD interval using three ofthe different formulas discussed above. The coefficients for eachformula were calculated by a linear regression analysis of data obtainedfrom a particular clinical population relating the optimum AVD to theintrinsic conduction parameters of the formula. In the tables, thesuffix appended to the pacing mode denotes the left ventricular pacingsite, either anterior (Ant) or the lateral free wall (Fwl).

TABLE 1 (AVD = k1 · AVI_(L) + k2 · AVI_(R) + k3) k1 k2 k3 LV-Ant 0.1630.769 −59.6 BV-Ant 0.063 1.008 −73.0 LV-Fwl −0.099 0.988 −64.3 BV-Fwl−0.126 0.857 −27.5

TABLE 2 (AVD = k1 · QRS + k2 · AVI_(R) + k3) k1 k2 k3 LV-Ant −1.3250.918 135.3 BV-Ant −0.835 1.041 49.0 LV-Fwl −0.459 0.911 −4.3 BV-Fwl−0.728 0.757 71.3

TABLE 3 (AVD = k1 · Q*S* + k2 · AQ* + k3 · AVI_(R) + k4) k1 k2 k3 k4LV-Ant −0.677 0.808 0.273 67.5 BV-Ant −0.706 0.615 0.610 47.2 LV-Fwl−0.337 0.157 0.797 −0.46 BV-Fwl −0.312 0.339 0.482 31.6

The optimum AVD interval may, in certain instances, differ dependingupon whether the ventricular pace or paces are delivered after an atrialsense or after an atrial pace (i.e., whether the paces are delivered inaccordance with an atrial tracking mode or an AV sequential pacingmode). It may therefore be desirable to compute separate optimum AVDintervals for the two types of pacing which the implantable device maythen use depending upon whether the AVD is initiated by an atrial senseor an atrial pace. Thus, with any of the formulas described above, anoptimum AVD delay for use following an atrial pace may be computed withan intrinsic AV interval or intervals measured after an atrial pace,while an optimum AVD delay for use following an atrial sense may becomputed with an intrinsic AV interval or intervals measured after anintrinsic atrial beat.

b. Optimal Adjustment of Biventricular Offset Interval

As described above, the amount of pre-excitation relative to an atrialbeat that is provided to one or both ventricles by resynchronizationpacing is determined by the AVD interval. Although it is believed that aprimary factor in optimizing ventricular resynchronization pacing isoptimal selection of the AVD interval, many patients exhibit furtherimprovement in systolic function with optimal selection of abiventricular offset (BVO) interval (also referred to as the LV offsetinterval). That is, although certain patients may exhibit optimumimprovement with either LV-only pacing (i.e., where only the leftventricle is pre-excited with the right ventricle being intrinsicallyactivated via conduction through the AV node) or biventricular pacingwith an arbitrarily chosen biventricular offset, others requirebiventricular offset pacing with an optimized biventricular offset foroptimum improvement in systolic function. For this latter group ofpatients, it has been found that there is a predictive relationshipbetween the intrinsic right-to-left ventricle conduction time and thebest biventricular offset. Preferably, the relationship is expressed asa linear formula:BVO=k1·Δ_(RL) +k2where BVO is the optimal biventricular offset interval, Δ_(RL) is themeasured intrinsic right-to-left ventricle conduction time, and k1 andk2 are specified coefficients obtained empirically. Applying thisformula results in an optimized biventricular offset for those patientswho require it in order to achieve maximum improvement in systolicfunction with resynchronization pacing.

The Δ_(RL) parameter may be obtained from electrogram signals generatedby the right and left ventricular sensing channels of the implantabledevice. The Δ_(RL) parameter may be obtained by the implantable devicemeasuring the time interval between right and left ventricular senses,by the external programmer computing the time interval between RV and LVsenses from an electrogram or sense markers transmitted from theimplantable device, or by a clinician measuring the distance between RVand LV sense markers in an electrogram display generated by the externalprogrammer. An estimate of the Δ_(RL) parameter may be measured by othermeans and used in a linear equation with different coefficients topredict the optimum biventricular offset. Specific estimates of theΔ_(RL) include the duration of the QRS interval measured on a surfaceECG or on a leadless ECG recording from the implanted device, and theQ*S* interval measured from an intracardiac lead electrogram as theinterval from the start of left ventricular depolarization to the end ofleft ventricular depolarization in the electrogram. The Δ_(RL) parametermay be either a single measurement or an average measurement taken overa number of beats. In one representative patient population, thefollowing formula was found to calculate an optimum biventricular offsetinterval:BVO=−0.333·Δ_(RL)−20where the specified coefficients were obtained by a regression analysis,and the convention is adopted that a positive Δ_(RL) value representsthe LV sense lagging the RV sense. The system may be programmed toautomatically set the programmed biventricular offset interval inaccordance with the computed optimum biventricular offset interval or torecommend to an operator of the external programmer that the programmedbiventricular offset interval be set to the computed optimumbiventricular offset interval.

FIG. 7 illustrates as steps F1 through F12 an exemplary implementationof the above-described method for determining the optimum biventricularoffset interval as could be executed by an appropriately programmedprocessor of the implantable cardiac device or external programmer. Inthis embodiment, the optimum BVO is obtained according to the followingformula:BVO=k1·Δ_(RL) +k2where Δ_(RL) is the interval between a right ventricular sense and aleft ventricular sense on electrocardiograms. The ventricular sense maybe detected by the implantable device from an electrogram using athreshold criterion similar to that used for detecting chamber senses.Alternative formulas for calculating the BVO using differentinterventricular conduction delay parameters may also be employed,examples of which are:BVO=k1·QRS+k2BVO=k1·Q*S*+k2where QRS is the width width of the QRS complex as determined from asurface electrocardiogram and Q*S* is the duration of ventriculardepolarization measured as the interval from the start of leftventricular depolarization to the end of left ventricular depolarizationin an electrogram. The specified coefficients are k1 and k2, wheredifferent sets of coefficients are used depending upon the sign andmagnitude of the Δ_(RL) value. For instance as illustrated in FIG. 7, ifΔ_(RL) is larger than a threshold value, T1, a set of LV-firstcoefficients is used, otherwise if Δ_(RL) is less than a thresholdvalue, T2, a set of RV-first coefficients is used. When Δ_(RL) isgreater than T1, there is a right-to-left ventricular conduction delaythat can be corrected by pacing the LV first and the RV second;therefore the LV-first coefficients provide a BVO for pacing the LVbefore the RV. When Δ_(RL) is less than T2, there is a left-to-rightventricular conduction delay that can be corrected by pacing the RVfirst and the LV second; therefore the RV-first coefficients provide aBVO for pacing the RV before the LV. Example LV-first coefficients basedon population data are k1=−0.333 and k2=−20. Example RV-firstcoefficients based on population data are k1=0 and k2=0. Also differentcoefficient sets can be selected based on different locations of theleft and right ventricular sensing leads. For example, there can be twoLV-first coefficient sets: one to be used when the left ventricular leadis located near the LV septum and another to be used when the leftventricular lead is located near the LV lateral wall. Also differentcoefficient sets can be selected dependent on whether Δ_(RL) is measuredwhen atrial sensing or when atrial pacing. When Δ_(RL) is between T1 andT2, the interventricular conduction delay is too small to be correctedwith sequential biventricular pacing; so the BVO is set to zero forsimultaneous biventricular pacing. Example threshold values based onpopulation data are T1=20 ms and T2=−20 ms.

Still referring to FIG. 7, after the optimum BVO is calculated, thesystem selects which chambers are to be paced in delivering ventricularresynchronization. The system determines whether the BVO is smaller thana threshold T3 or if the difference of AVD and BVO is greater than theright intrinsic atrio-ventricular delay (AV_(R)) less an offset S1, andin either case, selects the LV-only chamber for pacing. An examplethreshold value is T3=−80 ms. When BVO is less than this value, theconduction from the first LV pace is likely to spread to the rightventricle before it would be paced. Or the RV pace may occur afterintrinsic conduction has spread to the right ventricle. This isindicated when the RV pace occurs after an offset S1 from the AV_(R),where S1 may be for example between 0 and 30 ms. In either case, theeffect of the sequential biventricular pacing is equivalent to LV-onlypacing. Similarly, the system determines whether the opposite is true,that is whether the BVO is larger than a threshold T4 or if the sum ofAVD and BVO is greater than the left intrinsic atrio-ventricular delay(AV_(L)), and in either case, selects the RV-only chamber for pacing. Anexample threshold value is T4=80 ms. If none of these exceptions occur,the system selects the biventricular chambers for pacing with thecalculated biventricular offset interval.

3. Exemplary System for Determining Pre-Excitation Timing Parameters

A system made up of an implantable device and an external programmer (orthe implantable device alone) may thus be programmed to determineoptimum values for the AVD interval and the biventricular offsetinterval. In the following description of an exemplary embodiment, thesystem determines an optimum biventricular offset interval frommeasurement of the patient's Δ_(RL) conduction delay. The optimum AVDinterval for use with the computed biventricular offset is eitherdetermined clinically or determined by the system from a formulautilizing conduction delay alone or combined with QRS width measurementsas described above. Most patients with systolic dysfunction which can beimproved by resynchronization therapy have conduction deficits whichcause delayed intrinsic activation of the left ventricle (e.g., leftbundle branch blocks). Systolic function is improved in these patientswith resynchronization therapy that pre-excites the left ventricle. Theformulas for computing an optimum AVD interval as described above thengive an AVD interval representing the time between an atrial sense orpace and a left ventricular pace. The implantable device, however, maydeliver ventricular paces in accordance with a pacing mode based uponright ventricular timing. In that case, the AVD interval used by thedevice is an escape interval started by an atrial sense or pace which isstopped by a right ventricular sense and results in a right ventricularpace upon expiration. In order to reconcile these two types of AVDintervals, the computed optimum biventricular offset is subtracted fromthe computed optimum AVD interval to give an AVD interval which can thenbe used by the implantable device with a pacing mode based upon rightventricular timing. For example, if the computed optimum biventricularoffset were −20 ms (i.e., the LV pace leads the RV pace by 20 ms) andthe computed optimum AVD interval for left ventricular pre-excitationwere 100 ms (i.e., the time between an atrial sense or pace and a leftventricular pace is optimally 100 ms), then the actual AVD delay used bythe implantable device using RV-based timing would be 100−(−20)=120 ms,which is the time between an atrial sense or pace and a rightventricular pace.

The steps performed by the system in this exemplary embodiment in orderto select optimum pre-excitation timing parameters are as follows.First, the intrinsic Δ_(RL) parameter is determined, eitherautomatically by the implanted device or external programmer or bymanually measuring the interval from the implanted device's RV sense toLV sense event markers during intrinsic conduction on the electrogramdisplay. In order to measure the intrinsic Δ_(RL) interval, theimplantable device is set to a temporary sensing diagnostic mode, suchas ODO mode. In the case where the system includes an externalprogrammer, transmission of real-time atrial and ventricular markers tothe external programmer is also enabled. After the device hastransitioned into temporary sensing mode, the implantable device, or anoperator of the external programmer, should wait for at least 10 cardiaccycles before measuring the intrinsic Δ_(RL) interval, and a typicalmeasurement should be made when the intrinsic Δ_(RL) is stable.Averaging Δ_(RL) values from several cycles may be helpful. Thefollowing events must be avoided when making a measurement: ventricularpacing, intrinsic atrial rate above the programmed maximum trackingrate, premature ventricular contractions, and abnormal atrial orventricular sensing. The same considerations may also apply whenmeasuring any intrinsic conduction parameter. The intrinsic Δ_(RL)measurement is then used to calculate the optimum biventricular offsetfrom a formula as described above or used to lookup an optimumbiventricular offset from an equivalent table. Once the optimumbiventricular offset is determined, an optimum AVD interval iscalculated or otherwise obtained. The system may measure intrinsic AVconduction delays and the ventricular depolarization duration in orderto compute the optimum AVD interval from a formula as described above.After determination of the optimum AVD interval, the biventricularoffset may be subtracted from the optimum AVD interval to give aprogrammed AVD interval for use in RV-based pacing.

In certain instances, the system may modify the biventricular offsetinterval from its initially computed optimum value. For example,tachyarrhythmia detection based on right ventricular senses is affectedby negative offset pacing of the left ventricle due to a cross-chambersensing refractory period in the right ventricular sensing channel whichis initiated by a left ventricular pace. (See U.S. patent applicationSer. No. 10/037,444, filed on Oct. 25, 2001, the disclosure of which ishereby incorporated by reference.) That is, even while pacing the heartin a bradycardia resynchronization pacing mode, most cardiac rhythmmanagement devices still monitor intrinsic cardiac activity for theonset of tachyarrhythmias. The device detects a ventriculartachyarrhythmia by measuring the time interval between successiveventricular depolarizations and comparing the measured interval to aspecified limit value. That limit value is referred to as thetachyarrhythmia rate threshold interval (TRTI) and corresponds to thelowest intrinsic rate that is to be regarded as a tachyarrhythmia,referred to as the tachyarrhythmia rate threshold (TRT). The effectivelower limit for tachyarrhythmia detection corresponds to a maximumtachyarrhythmia rate threshold interval MTRTI that may be expressed interms of the pacing interval PI and the negative biventricular offsetinterval BVO as:MTRTI=PI−BVOThus, decreasing the pacing interval and/or increasing the biventricularoffset raises the lowest ventricular rate which can be detected as atachyarrhythmia. The system may therefore be programmed to compare themaximum pacing rate (e.g., a maximum tracking rate in the case of anatrial tracking pacing mode or a maximum sensor indicated rate in thecase of a rate-adaptive pacing mode) and the computed optimumbiventricular offset interval to determine if tachyarrhythmia detectionwould be unduly compromised. The system may then either automaticallyshorten the biventricular offset interval or display a message advisingthe clinician to do so. For example, given a particular maximum trackingrate, the system may automatically shorten a computed biventricularoffset interval so that the lowest ventricular rate detectable as atachyarrhythmia is 5 bpm less than the programmed TRT parameter (oradvise the clinician to do so via the external programmer).

The system may also incorporate logic for modifying the optimumbiventricular offset interval after determination of the more importantAVD interval. For example, the system might determine that a zerobiventricular offset would be better for the patient. If a zerobiventricular offset would be better, the system could either recommendthat the biventricular offset be re-programmed to zero or automaticallydo so. This may be programmed to occur under any of the followingcircumstances: 1) positive biventricular offset has been programmed(when a positive biventricular offset should only be programmed as aresult of direct hemodynamic testing or other evidence ofeffectiveness), 2) the system determines the patient is likely to be aweak responder or non-responder to CRT, as indicated by either a QRS<150msec or a QRS<160 msec and the LV lead being in an anterior vein,indicating small baseline asynchrony, which requires a reduced degree ofresynchronization that is delivered with longer AV delays resulting infusion, or 3) the RV activation is delayed compared to the LV activation(i.e., the intrinsic Δ_(RL) is negative), suggesting a right bundlebranch block pattern, which usually means the patient is a weakresponder.

4. Optimal Adjustment of Right and Left Atrio-Ventricular Delays forSequential Biventricular Pacing

Another embodiment of a system for determining pre-excitation timingparameters for cardiac resynchronization therapy determines thebiventricular offset interval by selecting two AVD intervals: 1)AVD_(1ST), which is the atrio-ventricular delay to the first pacedventricle, and 2) AVD_(2ND), which is the atrio-ventricular delay to thesecond paced ventricle. The difference between AVD_(2ND) and AVD_(1ST)is the biventricular offset interval, which is always a positive value.Either the right or left ventricle may be paced first. The optimum AVDintervals are either determined clinically or determined by the systemfrom a formula utilizing conduction delay alone or combined with QRSwidth measurements as described above. In one case, the optimum AVDintervals are determined for atrial tracking, when the AV intervals areinitiated by an atrial sense. In another case, the optimum AVD intervalsare determined for AV sequential pacing, when the AV intervals areinitiated by an atrial pace. In this embodiment, four optimum AV delayintervals are selected by the system and can be independently programmedinto the implantable cardiac device by an external programmer: 1) rightsensed AVD, 2) left sensed AVD, 3) right paced AVD, and 4) left pacedAVD. When the left ventricle is paced first, left sensed and paced AVDintervals are set to the optimum sensed and paced AVD_(1ST) intervals,and the right sensed and paced AVD intervals are set to the optimumsensed and paced AVD_(2ND) intervals. The opposite assignments are madewhen the right ventricle is paced first.

FIG. 8 shows as steps G1 through G11 an exemplary method for determiningthe optimum AVD_(1ST) and AVD_(2ND) as could be executed by anappropriately programmed processor of the implantable cardiac device orexternal programmer. In this embodiment, the optimum AVD intervals areobtained according to the following formulas:AVD _(1ST) =k1·AV _(1ST) +k2·AV _(2ND) +k3AVD _(2ND) =k4·AV _(1ST) +k5·AV _(2ND) +k6where AV_(1ST) is the intrinsic interval between an atrial event (sensedor paced) and the right or left ventricular sense whichever is first,and AV_(2ND) is the intrinsic interval between an atrial event andwhichever is the second ventricular sense on electrocardiograms.Alternative formulas for calculating the AVD intervals may also beemployed as illustrated in the section (Optimal adjustment of AVD)above. In the embodiment in FIG. 8, the coefficient sets (k1,k2,k3) and(k4,k5,k6) for the AVD interval formulas are based upon the sign andmagnitude of the Δ_(RL) value, which is the right-to-left ventricularconduction delay. For instance as illustrated in FIG. 8, if Δ_(RL) islarger than a threshold value, T1, the left ventricle is selected to bepaced first and a set of LV-first coefficients is used, otherwise ifΔ_(RL) is less than a threshold value, T2, the right ventricle isselected to be paced first and a set of RV-first coefficients is used.Example LV-first coefficients for AVD_(1ST) based on population data arepresented in Table 1, and example coefficients for AVD_(2ND) are shownin Table 4. Different coefficient sets can be selected based ondifferent locations of the left and right ventricular sensing leads, asillustrated in the tables. Also different coefficient sets can beselected dependent on whether Δ_(RL) is measured when atrial sensing orwhen atrial pacing. When Δ_(RL) is between T1 and T2, theinterventricular conduction delay is too small to be corrected withsequential biventricular pacing. In this case, the AVD_(1ST) iscalculated based on intrinsic conduction intervals and the AVD_(2ND) isset equal to the AVD_(1ST) for simultaneous biventricular pacing.

TABLE 4 (AVD_(2ND) = k4 · AVI_(L) + k5 · AVI_(R) + k6) k4 k5 k6 LV-Ant0.496 0.436 −39.6 BV-Ant 0.396 0.675 −53.0 LV-Fwl 0.234 0.655 −44.3BV-Fwl 0.207 0.524 −7.5

Still referring to FIG. 8, after the optimum AVD intervals arecalculated, the system selects which chambers are to be paced indelivering ventricular resynchronization. The system determines whetherthe biventricular offset interval is larger than a threshold T3 or ifthe AVD_(2ND) is greater than the right intrinsic atrio-ventriculardelay (AV_(R)) less an offset S1. In either case, the first-pacedchamber only is selected for pacing. If neither is the case, the systemselects the biventricular chambers for pacing with the calculated AVDintervals.

5. Adjustment of Other Pacing Parameters

FIG. 3 shows an exemplary algorithm for obtaining the intrinsicconduction parameters used to calculate the pre-excitation timingparameters by the procedures described above as well as select otheroptimum pacing parameters. (As the terms are used herein, “setting” or“selecting” a particular pacing parameter should be taken to mean eitherrecommending the selected parameter to an operator of the externalprogrammer or automatically configuring the implantable device with theselected parameter.) The algorithm would be executed during a dataacquisition period while no pacing therapy is applied by the implantabledevice. At step B1, the sensing channels for obtaining the RV and LVelectrograms are selected, and a beat counter variable is initialized.When an atrial sense occurs, a beat is detected at step B2 and the beatcounter variable is incremented. If a subsequent ventricular sense doesnot occur, the beat is discarded as ectopic at step B3, and, if the beatcounter variable does not exceed a specified limit value as tested forat step B4, the algorithm awaits the next beat detection at step B2.Otherwise the intrinsic conduction parameters AV_(L), AV_(R), AQ*_(L),Q*V_(L), and Q*S*_(L) are measured from the RV and LV electrogramsignals generated during the beat and stored at step B5. AV_(L), AV_(R),AQ*_(L), and Q*S*_(L) are as defined above, and Q*V_(L) is the measuredinterval from the start of left ventricular depolarization to a leftventricular sense. At step B6, the beat counter variable is comparedwith another specified limit value (in this case, fifteen) and, if thelimit value has not been reached, the algorithm waits for the next beat.After conduction parameters from fifteen beats have been stored, themean, median, and standard deviation values of the parametermeasurements are calculated at step B7. A step B8, the ratio of thestandard deviation to the mean is calculated for all of conductionparameter measurements and compared to a specified limit value C, wherein the case of AV_(L) and AV_(R), C=0.25, while in the case of AQ*_(L),Q*V_(L), and Q*S*_(L), C=0.4. If the calculated ratios are all less thanC, an average value of the stored measurement for each conductionparameter is registered and used to represent that conduction parameterat step B9. The average value of the stored measurements used in thisembodiment is a median, but other embodiments may employ a mean,standard deviation, or similar statistic. In addition, aninterventricular conduction delay parameter Δ_(L-R) is calculated as thedifference between the average value of AV_(L) and the average value ofAV_(R).

FIG. 4 illustrates an algorithm that may be executed by the system inorder to determine the left ventricular lead location, which informationis used by the algorithm for calculating the AVD illustrated in FIG. 2If manual input of the parameter is available, as determined at step C1,the algorithm sets the lead location according to the manual input atstep C2. Otherwise, the representative value of the Q*V_(L) parameter isrecalled at step C3 and compared with a limit value (in this case, 100ms) at step C4. If the Q*V_(L) parameter is less than the limit value,the lead location is set as anterior at step C5. Otherwise, the leadlocation is set as the left ventricular free wall at step C6.

The system may also use measured intrinsic conduction parameters tocompute other pacing parameters for optimal delivery of therapy. Suchparameters may include which heart chambers are to be paced and whichalternative LV pacing sites should be used to pace the left ventricle.The left ventricular lead used for sensing and pacing may be a bipolaror multi-polar lead, which thus makes available to the implantabledevice alternative sites for delivering paces to the left ventricle. Theselection between alternative LV pacing sites for optimal delivery ofresynchronization therapy can be made based upon the relative intrinsicAV conduction delays measured from the different sites. Under mostcircumstances, it is desirable to pre-excite the left ventricular regionthat suffers the most conduction delay during an intrinsic contractionin order to compensate for that delay. For example, if two LV pacingsites L1 and L2 are available, the intrinsic conduction parametersAV_(L1) and AV_(LV2) can be measured which are the intervals between anatrial sense and a left ventricular sense detected from electrogramsgenerated at sites L1 and L2, respectively. The pacing site which isexcited later during an intrinsic beat as reflected by a longer AV delayinterval can then be selected as the LV pacing site.

FIG. 5 illustrates an exemplary algorithm for obtaining the AV_(L1) andAV_(LV2) parameters and calculating their difference, designated asΔ_(L1-L2). At step D1, the beat counter variable is reset, and theimplantable device is configured to receive electrograms fromalternative sites L1 and L2. In the particular device illustrated inFIG. 1, this would involve configuring two sensing channels withelectrodes at the L1 and L2 sites via the switching network 70. Steps D2through D4 discard ectopic beats and are similar to previously describedsteps B2 through B4 of FIG. 3. At step D5, the conduction parametersAV_(L1) and AV_(LV2) are measured from the two electrograms. At step D6,the beat counter variable is compared with another specified limit value(in this case, five) and, if the limit value has not been reached, thealgorithm waits for the next beat. After measurements of the parametersfrom five beats have been stored, the mean, median, and standarddeviation values of the AV_(L1) and AV_(LV2) measurements are calculatedat step D7. At step D8, the ratio of the standard deviation to the meanis calculated and, if found to be less than a specified limit value (inthis case, 0.25), Δ_(L1-L2) is calculated as the difference between themedian values of AV_(L1) and AV_(LV2). The system may then be programmedto select the LV pacing site in accordance with the calculated Δ_(L1-L2)parameter, an exemplary procedure for which is illustrated by FIG. 6. Atstep E1, the system checks if a pacing site L2 is available and, if not,selects the default site L1 at step E5. If both sites L1 and L2 areavailable, the Δ_(L1-L2) parameter is recalled at step E2 and comparedwith zero at step E3. If Δ_(L1-L2) is negative, indicating that site L1is excited earlier than site L2 during an intrinsic contraction, site L2is selected as the LV pacing site at step E4. If Δ_(L1-L2) is greaterthan or equal to zero, indicating that site L1 is excited later thansite L2 or at the same time, site L1 is selected as the LV pacing siteat step E5.

6. System Implementation

The above-described algorithms may thus be used by a system includingthe implantable device and an external programmer or the implantabledevice alone in order to set one or more pacing parameters for theoptimal delivery of resynchronization therapy. One or more of thealgorithms may be executed by the system in order to initialize theparameters prior to delivering resynchronization therapy and/or executedperiodically in order to update the parameters. The implantable cardiacrhythm management device would include sensing channels for generatingelectrogram signals corresponding to electrical activity in an atriumand both the right and left ventricles, right and left ventricularpacing channels for delivering pacing pulses to the right and leftventricles, and a controller for controlling the output of pacing pulsesand interpreting electrogram signals, where the controller is programmedto pace at least one ventricle in a manner defined by at least onepre-excitation timing parameter. The system is programmed to measure (orenable measurement of) one or more intrinsic conduction parametersduring an intrinsic beat from electrogram signals generated in thesensing channels of the implantable device, including an intrinsicatrio-ventricular delay interval in each ventricular sensing channel, aduration of ventricular depolarization, and a delay between right andleft ventricular activation. The system may then be further programmedto select between a biventricular, right ventricular-only, or leftventricular-only pacing mode based upon the measured intrinsicconduction parameters and/or select the value of the pre-excitationtiming parameter according to a formula which includes a linearcombination of the measured intrinsic conduction parameters as definedby specified coefficients. The pre-excitation timing parameter may bethe AVD and/or an offset interval for delivering biventricular or leftventricular-only pacing. The system may be further programmed to selectbetween a biventricular, right ventricular-only, or leftventricular-only pacing mode based upon the measured intrinsicconduction parameters and a specified location of a left ventricularlead used by the left ventricular sensing and pacing channels, where thelocation of the left ventricular lead is specified by user input ordetermined from the value of Q*V_(L). The device may also be equippedwith a plurality of sensing/pacing electrodes, sense amplifiers, pulsegenerators, and a switching network operated by the controller forconfiguring a sensing channel by connecting a selected electrode pair toa selected sense amplifier and for configuring a pacing channel byconnecting a selected electrode pair to a selected pulse generator. Theplurality of sensing/pacing electrodes may include at least twoalternative left ventricular electrodes located at different leftventricular sites, and the measured intrinsic conduction parameters mayinclude AV conduction delays measured from the at least two alternativeleft ventricular electrodes. The system may then be programmed to selectbetween the alternative left ventricular electrodes for configuring theleft ventricular pacing channel based upon the intrinsic AV conductiondelays measured from each alternative left ventricular electrode such asby configuring the left ventricular pacing channel with whichever of thealternative left ventricular electrodes has the longest intrinsic AVconduction delay measured from it.

In one embodiment, the system for selecting optimum pacing parametersincludes the implantable device and an external programmer incommunication therewith. The processors of the implantable device and ofthe external programmer are programmed to perform the steps forselecting optimum pacing parameters as described above, where thecomputational burden may be shared between the two processors in anymanner deemed to desirable. The implantable device may collect intrinsicconduction data and transmits the data to the external programmer invarious alternative forms. For example, the transmitted intrinsicconduction data may constitute raw electrograms, markers representingparticular events and the times of their occurrence, or the derivedconduction parameters themselves. Processing of the intrinsic conductionparameters in order to compute optimum pacing parameters by thealgorithms described above may then be done entirely by the externalprogrammer or shared between the external programmer and the implantabledevice. After computation of the optimum pacing parameter values, theexternal programmer may then automatically program the implantabledevice with the computed optimum pacing parameter settings or presentthe optimum values to a clinician operating the external programmer inthe form of a recommendation.

Although the invention has been described in conjunction with theforegoing specific embodiments, many alternatives, variations, andmodifications will be apparent to those of ordinary skill in the art.Other such alternatives, variations, and modifications are intended tofall within the scope of the following appended claims.

1. A system for setting one of more pacing parameters used by animplantable cardiac rhythm management device in delivering cardiacresynchronization therapy, comprising: an implantable cardiac rhythmmanagement device which includes: an atrial sensing channel forgenerating electrogram signals corresponding to electrical activity inan atrium; right and left ventricular sensing channels for generatingelectrogram signals corresponding to electrical activity in the rightand left ventricles, respectively; right and left ventricular pacingchannels for delivering pacing pulses to the right and left ventricles,respectively; a controller for controlling the output of pacing pulsesand interpreting electrogram signals, wherein the controller isprogrammed to deliver a left ventricular pace and a right ventricularpace separated by a programmed biventricular offset interval inaccordance with a demand pacing mode; and, a telemetry interface; anexternal programmer with associated display and input means incommunication with the implantable device via the telemetry interface;wherein the system is programmed to generate signals from which thedelay between right ventricular and left ventricular activation duringan intrinsic beat, referred to as the Δ_(RL) interval, may be measured;and, wherein the system is programmed to compute an optimumbiventricular offset interval in accordance with a formula whichexpresses the optimum biventricular offset interval as a function of themeasured Δ_(RL) interval.
 2. The system of claim 1 wherein the system isprogrammed to measure the Δ_(RL) interval from electrogram signalsreceived by the implantable device.
 3. The system of claim 1 wherein thecontroller of the implantable device is programmed to pace theventricles within a programmable atrio-ventricular delay (AVD) intervalafter an atrial sense in an atrial-tracking mode or an atrial pace in anAV sequential pacing mode.
 4. The system of claim 3 wherein the systemis programmed to measure at least one intrinsic atrio-ventricular delayinterval from electrogram signals during an intrinsic beat and computean optimum AVD interval in accordance with a formula which expresses theoptimum AVD interval as a function of the measured intrinsicatrio-ventricular delay interval.
 5. The system of claim 4 wherein thesystem is programmed to measure right and left intrinsicatrio-ventricular delay intervals and a duration of ventriculardepolarization from electrogram signals and wherein the formula forcomputing the optimum AVD interval includes a linear combination of themeasured right and left intrinsic atrio-ventricular delays and themeasured duration of ventricular depolarization.
 6. The system of claim5 wherein the right intrinsic atrio-ventricular delay is measured as theinterval between an atrial sense and a right ventricular sensedesignated as AV_(R), the left intrinsic atrio-ventricular delay ismeasured as the interval between an atrial sense and the start of leftventricular depolarization in an electrogram designated as AQ*_(L), theduration of ventricular depolarization is measured as the interval fromthe start of left ventricular depolarization to the end of leftventricular depolarization in an electrogram designated as Q*S*, and theformula for computing the optimum AVD is:AVD=k₁AV_(R) +k ₂ AQ* _(L) +k ₃ Q*S*+k ₄ where k₁, k₂, k₃, and k₄ arespecified coefficients.
 7. The system of claim 4 wherein a rightintrinsic atrio-ventricular delay is measured as the interval between anatrial sense and a right ventricular sense designated as AV_(R), a leftintrinsic atrio-ventricular delay is measured as the interval between anatrial sense and a left ventricular sense designated as AV_(L), and theformula for computing the AVD is:AVD=k ₁ AV _(R) +k ₂ AV _(L) +k ₃ where k₁, k₂, and k₃, are specifiedcoefficients.
 8. The system of claim 4 wherein the intrinsicatrio-ventricular delay is measured as the interval between an atrialsense and a right ventricular sense designated as AVR, a duration ofventricular depolarization is measured as the interval from the start ofleft ventricular depolarization to the end of left ventriculardepolarization in an electrogram designated as Q*S*, and the formula forcomputing the optimum AVD is:AVD=k ₁ AV _(R) +k ₂ Q*S*+k ₃ where k₁, k₂, and k₃ are specifiedcoefficients.
 9. The system of claim 4 wherein specified coefficientsdefining a linear combination of the measured intrinsicatrio-ventricular delay interval and the measured duration ofventricular depolarization have been pre-derived from a linearregression analysis of clinical population data relating measuredintrinsic atrio-ventricular delay intervals and measured durations ofventricular depolarization to an optimum AVD for delivering cardiacresynchronization therapy as determined by measurement of a cardiacfunction parameter.
 10. The system of claim 4 wherein the system isprogrammed to automatically set the programmed AVD interval inaccordance with the computed optimum AVD interval.
 11. The system ofclaim 4 wherein the system is programmed to recommend to an operator ofthe external programmer that the programmed AVD interval be set to thecomputed optimum AVD interval.
 12. The system of claim 1 wherein theformula for computing the optimum biventricular offset interval BVO is:BVO=k ₁Δ_(RL))+k ₂ where k₁ and k₂ are specified coefficients.
 13. Thesystem of claim 12 wherein the specified coefficients defining therelationship between the optimum biventricular offset and the measuredΔ_(RL) interval have been pre-derived from a linear regression analysisof clinical population data relating measured Δ_(RL) intervals to anoptimum biventricular offset for delivering cardiac resynchronizationtherapy as determined by measurement of a cardiac function parameter.14. The system of claim 12 wherein the formula for computing the optimumbiventricular offset interval BVO is:BVO=−.333(Δ_(RL))−20.
 15. The system of claim 1 wherein the system isprogrammed to automatically set the programmed biventricular offsetinterval in accordance with the computed optimum biventricular offsetinterval.
 16. The system of claim 1 wherein the system is programmed torecommend to an operator of the external programmer that the programmedbiventricular offset interval be set to the computed optimumbiventricular offset interval.
 17. The system of claim 1 wherein themeasured Δ_(RL) interval represents an average measurement taken over aplurality of intrinsic beats.
 18. The system of claim 1 wherein thecomputed optimum biventricular offset interval is modified in order tomaintain a desired tachyarrhythmia rate threshold.
 19. A method forcomputing an optimum biventricular offset interval for deliveringbiventricular pacing therapy, wherein the biventricular offset intervalis the interval between right and left ventricular paces, comprising:measuring a delay between right ventricular and left ventricularactivation during an intrinsic beat, referred to as the Δ_(RL) interval;and, computing an optimum biventricular offset interval in accordancewith a formula which expresses the optimum biventricular offset intervalas a function of the measured Δ_(RL) interval.
 20. The method of claim19 wherein the formula for computing the optimum biventricular offsetinterval BVO is:BVO=k ₁(ARL)+k ₂ where k₁ and k₂ are specified coefficients defining therelationship between the optimum biventricular offset and the measuredΔ_(RL) interval which have been pre-derived from a linear regressionanalysis of clinical population data relating measured Δ_(RL) intervalsto an optimum biventricular offset for delivering cardiacresynchronization therapy as determined by measurement of a cardiacfunction parameter.